WO2016143160A1 - Système d'endoscope de balayage - Google Patents

Système d'endoscope de balayage Download PDF

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Publication number
WO2016143160A1
WO2016143160A1 PCT/JP2015/073153 JP2015073153W WO2016143160A1 WO 2016143160 A1 WO2016143160 A1 WO 2016143160A1 JP 2015073153 W JP2015073153 W JP 2015073153W WO 2016143160 A1 WO2016143160 A1 WO 2016143160A1
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WIPO (PCT)
Prior art keywords
frequency
amplitude
unit
scanning
actuator
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PCT/JP2015/073153
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English (en)
Japanese (ja)
Inventor
聡一郎 小鹿
篤義 嶋本
雅史 山田
Original Assignee
オリンパス株式会社
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by オリンパス株式会社 filed Critical オリンパス株式会社
Priority to DE112015006046.4T priority Critical patent/DE112015006046T5/de
Priority to CN201580077635.4A priority patent/CN107405044A/zh
Priority to JP2016520120A priority patent/JP6143953B2/ja
Publication of WO2016143160A1 publication Critical patent/WO2016143160A1/fr
Priority to US15/698,906 priority patent/US20180014719A1/en

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00172—Optical arrangements with means for scanning
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00002—Operational features of endoscopes
    • A61B1/00004—Operational features of endoscopes characterised by electronic signal processing
    • A61B1/00006—Operational features of endoscopes characterised by electronic signal processing of control signals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00163—Optical arrangements
    • A61B1/00165—Optical arrangements with light-conductive means, e.g. fibre optics
    • A61B1/00167—Details of optical fibre bundles, e.g. shape or fibre distribution
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/06—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements
    • A61B1/07—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor with illuminating arrangements using light-conductive means, e.g. optical fibres
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/2407—Optical details
    • G02B23/2461—Illumination
    • G02B23/2469—Illumination using optical fibres
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B23/00—Telescopes, e.g. binoculars; Periscopes; Instruments for viewing the inside of hollow bodies; Viewfinders; Optical aiming or sighting devices
    • G02B23/24—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes
    • G02B23/26—Instruments or systems for viewing the inside of hollow bodies, e.g. fibrescopes using light guides
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B26/00—Optical devices or arrangements for the control of light using movable or deformable optical elements
    • G02B26/08—Optical devices or arrangements for the control of light using movable or deformable optical elements for controlling the direction of light
    • G02B26/10—Scanning systems
    • G02B26/103—Scanning systems having movable or deformable optical fibres, light guides or waveguides as scanning elements
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B6/00—Light guides; Structural details of arrangements comprising light guides and other optical elements, e.g. couplings
    • G02B6/02—Optical fibres with cladding with or without a coating
    • G02B6/036—Optical fibres with cladding with or without a coating core or cladding comprising multiple layers

Definitions

  • the present invention relates to a scanning endoscope system, and more particularly to a scanning endoscope system that acquires an image by scanning a subject by driving a fiber with an actuator.
  • Such a scanning endoscope system is configured such that the tip of the fiber draws a circle by synthesizing the amplitudes in the X direction and the Y direction that are out of phase. Therefore, it is desirable to vibrate so that the tip of the fiber draws a straight track in each of the X direction and the Y direction. For this reason, a scanning type that uses a frequency apart from the resonance frequency by a predetermined hertz as a drive frequency that can stably control the vibration amplitude of the fiber based on the voltage applied to the actuator.
  • An endoscope system has been proposed (see, for example, Japanese Patent Application Laid-Open No. 2014-198189).
  • the frequency characteristics of the fiber amplitude shift to the low frequency side or the high frequency side.
  • the frequency characteristic shift is significant. If the frequency characteristic shifts, the change in amplitude with respect to the frequency is large in the frequency region around the resonance frequency, so that the vibration amplitude of the fiber cannot be controlled stably. For this reason, it is desirable to drive the fiber in a frequency band in which the change in amplitude is small, even in the case where the frequency characteristic is shifted due to environmental changes, in a frequency region that is a certain value away from the resonance frequency. In addition, since the frequency characteristics of the amplitude are different for each scope, it is desirable to set an optimum drive frequency region for each scope.
  • the scanning endoscope system described in Japanese Patent Application Laid-Open No. 2014-198189 uses a frequency band that is 100 Hz or more away from the resonance frequency as a driving frequency.
  • the frequency characteristic does not necessarily have frequency characteristics due to environmental changes. Even in the case of shifting, it is not always the frequency band in which the change in amplitude is small, so it cannot be said to be an optimum driving frequency region.
  • the present invention specifies a frequency region that is not easily affected by the shift of the frequency characteristic accompanying the environmental change, and uses the same frequency region as the drive frequency, thereby stably controlling the fiber amplitude regardless of the environmental change.
  • An object of the present invention is to provide a scanning endoscope system that can perform the above operation.
  • a scanning endoscope system guides illumination light for illuminating a subject and scans the illumination light on the subject, and a light guide unit for emitting the light from the exit end.
  • a scanning unit having an actuator that swings the output end of the light guide unit according to a voltage or current of an electric signal applied for the purpose, and an output end of the light guide unit according to a change in usage conditions of the scan unit
  • an application unit that applies the electric signal having a drive frequency that is a frequency at which the amount of change in the amplitude is equal to or less than a predetermined value even if the frequency characteristics of the amplitude at the time of swinging change.
  • FIG. The figure which shows an example of the spiral scanning path
  • FIG. which shows the relationship between the drive frequency of an actuator part, and the amplitude of the output end part of the fiber for illumination.
  • FIG. 1 is a diagram illustrating an example of a configuration of a main part of a scanning endoscope system according to an embodiment of the present invention.
  • the scanning endoscope system 1 includes a scanning endoscope 2 inserted into a body cavity of a subject, a main body device 3 to which the endoscope 2 can be connected,
  • the display device 4 is connected to the main body device 3, and the input device 5 is capable of inputting information and giving instructions to the main body device 3.
  • the scanning endoscope system 1 also has both an amplitude detector 100 and a frequency characteristic calculation unit 101.
  • the endoscope 2 as a scanning unit is configured to include an insertion unit 11 formed with an elongated shape that can be inserted into a body cavity of a subject.
  • a connector portion 61 for detachably connecting the endoscope 2 to the connector receiving portion 62 of the main body device 3 is provided at the proximal end portion of the insertion portion 11.
  • an electrical connector device for electrically connecting the endoscope 2 and the main body device 3 is provided inside the connector portion 61 and the connector receiving portion 62.
  • an optical connector device for optically connecting the endoscope 2 and the main body device 3 is provided inside the connector portion 61 and the connector receiving portion 62.
  • An illumination fiber 12 that is an optical fiber that guides the illumination light supplied from the light source unit 21 of the main body device 3 to the illumination optical system 14 in a portion from the proximal end portion to the distal end portion inside the insertion portion 11, and
  • the incident end including the light incident surface of the illumination fiber 12 as the light guide is disposed in the multiplexer 32 provided inside the main body device 3. Further, the emission end portion including the light emission surface of the illumination fiber 12 is disposed in the vicinity of the light incident surface of the lens 14 a provided at the distal end portion of the insertion portion 11.
  • the incident end portion including the light incident surface of the light receiving fiber 13 is fixedly disposed around the light emitting surface of the lens 14 b on the distal end surface of the insertion portion 11. Further, the emission end portion including the light emission surface of the light receiving fiber 13 is arranged in a duplexer 36 provided inside the main body device 3.
  • the illumination optical system 14 includes a lens 14a on which illumination light having passed through the light emission surface of the illumination fiber 12 is incident, and a lens 14b that emits illumination light having passed through the lens 14a to a subject.
  • an actuator portion 15 that is driven based on a drive signal supplied from the driver unit 22 of the main body device 3 is provided.
  • the illumination fiber 12 and the actuator unit 15 are arranged so as to have, for example, the positional relationship shown in FIG. 2 in a cross section perpendicular to the longitudinal axis direction of the insertion unit 11.
  • FIG. 2 is a cross-sectional view for explaining the configuration of the actuator unit.
  • a ferrule 41 as a joining member is disposed between the illumination fiber 12 and the actuator unit 15.
  • the ferrule 41 is made of, for example, zirconia (ceramic) or nickel.
  • the ferrule 41 is formed as a quadrangular prism, and side surfaces 42 a and 42 c that are perpendicular to the X-axis direction, which is the first axial direction orthogonal to the longitudinal axis direction of the insertion portion 11, Side surfaces 42b and 42d perpendicular to the Y-axis direction, which is the second axial direction perpendicular to the longitudinal axis direction of the insertion portion 11, are included.
  • the illumination fiber 12 is fixedly arranged at the center of the ferrule 41.
  • the ferrule 41 may be formed as a shape other than the quadrangular column as long as it has a column shape.
  • the actuator unit 15 includes a piezoelectric element 15a disposed along the side surface 42a, a piezoelectric element 15b disposed along the side surface 42b, and a piezoelectric element disposed along the side surface 42c. 15c and the piezoelectric element 15d arranged along the side surface 42d.
  • the piezoelectric elements 15a to 15d have polarization directions set individually in advance, and are configured to expand and contract in accordance with a drive voltage applied from a drive signal supplied from the main body device 3.
  • a non-volatile memory 16 for storing the driving conditions of the actuator unit 15 that is unique to each endoscope 2 is provided inside the insertion unit 11.
  • the drive conditions include a setting condition for the drive frequency of the actuator unit 15 calculated from the frequency characteristics of the amplitude of the illumination fiber 12 by a method described later.
  • the driving conditions stored in the memory 16 are determined when the connector portion 61 of the endoscope 2 and the connector receiving portion 62 of the main body device 3 are connected and the main body device 3 is turned on. 3 is read by the controller 25.
  • the setting condition of the drive frequency of the actuator unit 15 is stored in the memory 16 at an arbitrary timing before the user uses the endoscope 2 for the first time, for example, when the endoscope 2 is manufactured. Shall be.
  • the main unit 3 includes a light source unit 21, a driver unit 22, a detection unit 23, a memory 24, and a controller 25.
  • the light source unit 21 includes a light source 31a, a light source 31b, a light source 31c, and a multiplexer 32.
  • the light source 31a includes a laser light source, for example, and is configured to emit red wavelength band light (hereinafter also referred to as R light) to the multiplexer 32 when light is emitted under the control of the controller 25. Yes.
  • R light red wavelength band light
  • the light source 31b includes, for example, a laser light source, and is configured to emit green wavelength band light (hereinafter also referred to as G light) to the multiplexer 32 when light is emitted under the control of the controller 25. Yes.
  • G light green wavelength band light
  • the light source 31c includes, for example, a laser light source, and is configured to emit light in a blue wavelength band (hereinafter also referred to as B light) to the multiplexer 32 when light is emitted under the control of the controller 25. Yes.
  • B light a blue wavelength band
  • the multiplexer 32 multiplexes the R light emitted from the light source 31a, the G light emitted from the light source 31b, and the B light emitted from the light source 31c onto the light incident surface of the illumination fiber 12. It is configured to supply.
  • the driver unit 22 as the application unit is configured to generate a drive signal corresponding to the drive voltage applied to the actuator unit 15.
  • the driver unit 22 includes a signal generator 33, D / A converters 34a and 34b, and an amplifier 35.
  • the signal generator 33 is a predetermined drive signal as shown by a broken line in FIG. 3, for example, as a first drive signal for swinging the emission end of the illumination fiber 12 in the X-axis direction.
  • a voltage signal having a signal waveform obtained by performing the above modulation on a sine wave is generated and output to the D / A converter 34a.
  • the signal generator 33 is, for example, indicated by a one-dot chain line in FIG. 3 as a second drive signal for swinging the emission end of the illumination fiber 12 in the Y-axis direction based on the control of the controller 25.
  • FIG. 3 is a diagram illustrating an example of a signal waveform of a drive signal supplied to the actuator unit.
  • the D / A converter 34 a is configured to convert the digital first drive signal output from the signal generator 33 into an analog first drive signal and output the analog first drive signal to the amplifier 35.
  • the D / A converter 34 b is configured to convert the digital second drive signal output from the signal generator 33 into an analog second drive signal and output the analog second drive signal to the amplifier 35.
  • the amplifier 35 is configured to amplify the first and second drive signals output from the D / A converters 34 a and 34 b and output the amplified signals to the actuator unit 15.
  • FIG. 4 is a diagram illustrating an example of a spiral scanning path from the center point A to the outermost point B.
  • FIG. 5 is a diagram illustrating an example of a spiral scanning path from the outermost point B to the center point A.
  • illumination light is irradiated to a position corresponding to the center point A of the irradiation position of the illumination light on the surface of the subject.
  • the amplitudes (voltages) of the first and second drive signals increase from time T1 to time T2
  • the irradiation position of the illumination light on the surface of the subject starts from the center point A to the outside in the first spiral shape.
  • the outermost point B of the illumination light irradiation position on the surface of the subject is irradiated with the illumination light.
  • the amplitude (voltage) of the first and second drive signals decreases from time T2 to time T3
  • the irradiation position of the illumination light on the surface of the subject is the second spiral inward starting from the outermost point B.
  • illumination light is applied to the center point A on the surface of the subject.
  • the actuator unit 15 is emitted to the subject through the emission end by swinging the emission end of the illumination fiber 12 based on the first and second drive signals supplied from the driver unit 22.
  • the illumination light irradiation position can be displaced along the spiral scanning path shown in FIGS. 4 and 5. Further, the amplitudes of the first and second drive signals supplied from the driver unit 22 to the actuator unit 15 are maximized in the vicinity of time T2 or time T2. Further, when the spiral scanning path of FIGS. 4 and 5 is given as an example, the scanning range of the endoscope 2 is on the inner side of the outermost peripheral path including the outermost point B of the spiral scanning path. It is shown as a region to which it belongs and changes in accordance with the maximum amplitude of the drive signal supplied to the actuator unit 15.
  • the detection unit 23 includes a duplexer 36, detectors 37a, 37b, and 37c, and A / D converters 38a, 38b, and 38c.
  • the demultiplexer 36 includes a dichroic mirror and the like, and separates the return light emitted from the light emitting surface of the light receiving fiber 13 into light for each of R (red), G (green), and B (blue) color components. And it is comprised so that it may radiate
  • the detector 37a includes, for example, an avalanche photodiode and the like, detects the intensity of the R light output from the duplexer 36, generates an analog R signal corresponding to the detected intensity of the R light, and generates A It is configured to output to the / D converter 38a.
  • the detector 37b includes, for example, an avalanche photodiode, detects the intensity of the G light output from the branching filter 36, generates an analog G signal corresponding to the detected intensity of the G light, and generates A It is configured to output to the / D converter 38b.
  • an avalanche photodiode detects the intensity of the G light output from the branching filter 36, generates an analog G signal corresponding to the detected intensity of the G light, and generates A It is configured to output to the / D converter 38b.
  • the detector 37c includes, for example, an avalanche photodiode and the like, detects the intensity of the B light output from the demultiplexer 36, generates an analog B signal corresponding to the detected intensity of the B light, and generates A It is configured to output to the / D converter 38c.
  • the A / D converter 38a is configured to convert the analog R signal output from the detector 37a into a digital R signal and output it to the controller 25.
  • the A / D converter 38b is configured to convert the analog G signal output from the detector 37b into a digital G signal and output it to the controller 25.
  • the A / D converter 38c is configured to convert the analog B signal output from the detector 37c into a digital B signal and output it to the controller 25.
  • various parameters for causing the light sources 31a to 31c to emit light, and amplitude and phase difference for specifying the signal waveform in FIG. Stores information including parameters.
  • the controller 25 is configured by an integrated circuit such as an FPGA (Field Programmable Gate Array). Further, the controller 25 detects whether or not the insertion portion 11 is electrically connected to the main body device 3 by detecting the connection state of the connector portion 61 in the connector receiving portion 62 via a signal line or the like (not shown). It is configured to be able to.
  • the controller 25 includes a light source control unit 25a, a scanning control unit 25b, and an image generation unit 25c.
  • the light source control unit 25a is configured to control the light source unit 21 based on the control information read from the memory 24, for example, to cause the light sources 31a to 31c to emit light simultaneously.
  • the scanning control unit 25b as the setting unit is described above.
  • the drive frequency condition of the actuator unit 15 stored in the memory 16 is read.
  • the driving conditions unique to the endoscope 2 including the driving frequency condition read from the memory 16 and the control information read from the memory 24 for example, to generate a driving signal having a signal waveform as shown in FIG. Control is performed on the driver unit 22.
  • the image generation unit 25c detects the latest scanning path based on the signal waveform of the drive signal generated according to the control of the scanning control unit 25b, and corresponds to the irradiation position of the illumination light on the detected scanning path.
  • the pixel position of the raster scan format to be identified is specified, and the luminance value indicated by the digital signal output from the detection unit 23 is mapped to the specified pixel position to generate an observation image for one frame, and the generated 1
  • the observation images for the frames are sequentially output to the display device 4.
  • the image generation unit 25c is configured to perform processing for displaying a predetermined character string or the like on the display device 4.
  • the display device 4 includes, for example, a monitor and is configured to display an observation image output from the main device 3.
  • the input device 5 includes, for example, a keyboard or a touch panel.
  • the input device 5 may be configured as a separate device from the main body device 3 or may be configured as an interface integrated with the main body device 3.
  • the amplitude detector 100 is configured to detect the peristaltic width (amplitude) of the emission end of the illumination fiber 12 when the actuator unit 15 is driven to perturb the illumination fiber 12.
  • a general amplitude detection sensor such as an optical position sensor (Position Sensitive Detector, PSD) can be used.
  • PSD Position Sensitive Detector
  • the frequency characteristic calculation unit 101 is based on a change in environment around the endoscope 2 based on the relationship between the amplitude of the emission end of the illumination fiber 12 input from the amplitude detector 100 and the drive frequency of the actuator unit 15.
  • the drive frequency region of the actuator unit 15 that can obtain a stable amplitude is calculated.
  • a method for calculating the drive frequency region will be described.
  • FIG. 6 is a diagram illustrating the relationship between the drive frequency of the actuator unit and the amplitude of the emission end of the illumination fiber.
  • the amplitude of the emission end of the illumination fiber 12 has a maximum value when the drive frequency of the actuator unit 15 is the resonance frequency fs.
  • the amplitude of the emission end portion is abruptly decreased.
  • the amplitude is substantially constant.
  • an upper limit value (first threshold value) of the slope of the frequency characteristic is set in advance based on an allowable amount of change in amplitude before and after the shift, and the illumination fiber 12 input from the frequency characteristic calculation unit 101 is set.
  • a frequency fl1 having a slope equal to the first threshold is obtained.
  • a frequency region having the frequency fl1 as a lower limit is set as a drive frequency region. It is desirable that the upper limit value of the slope of the frequency characteristic is substantially zero.
  • the amplitude of the exit end of the illumination fiber 12 has a substantially constant value, so that the inclination is substantially zero.
  • the frequency characteristic in a region within a predetermined value (for example, about 20 Hz) from the resonance frequency fs is not used for calculating the frequency fl, and the frequency fl1 is calculated using the frequency characteristic of a frequency that is a predetermined value or more away from the resonance frequency fs. .
  • a predetermined value for example, about 20 Hz
  • the frequency fl1 is set using a frequency characteristic in a range higher than the frequency fd, which is on the high frequency side by a predetermined value (for example, about 20 Hz) from the resonance frequency fs. calculate.
  • noise may enter the waveform due to slight external vibration transmitted to the illumination fiber 12.
  • the amplitude of the frequency at which the noise is generated becomes larger than usual, and a steep peak appears at the frequency. If the slope of the frequency characteristic including noise is calculated in this way, the slope of the frequency of the peak portion of the noise also becomes substantially zero, and a correct value may not be obtained as the frequency fl1.
  • the frequency fl1 at which the slope of the frequency characteristic becomes equal to the first threshold it is desirable to consider the continuity of the slope of the frequency characteristic. That is, in a certain frequency range, when the slope of the frequency characteristic is continuously below the first threshold, the frequency closest to the resonance frequency is selected from the frequencies at which the slope of the frequency characteristic is below the first threshold. Calculated as the frequency fl1.
  • a frequency fl1 ′ whose slope is equal to the first threshold value is calculated on the lower frequency side than the resonance frequency fs, and a frequency region whose upper limit is the frequency fl1 ′ is calculated. Set as drive frequency region.
  • a method for calculating the drive frequency region using the amplitude shift amount of the emission end of the illumination fiber 12 will be described with reference to FIG.
  • Examples of environmental changes that shift the frequency characteristics of amplitude include temperature changes and humidity changes.
  • a method of calculating the drive frequency region will be described by taking as an example a shift in frequency characteristics when the temperature changes as an environmental change.
  • FIG. 7 is a diagram for explaining the shift of the frequency characteristics of the amplitude of the exit end of the illumination fiber due to environmental changes.
  • the frequency characteristic of the amplitude of the exit end of the illumination fiber at normal temperature is indicated by a solid line.
  • the frequency characteristic of the amplitude of the emission end when the same illumination fiber is exposed to a high temperature environment is indicated by a one-dot chain line.
  • a normal room temperature for example, about 25 degrees Celsius
  • a temperature within the body temperature of the subject for example, about 37 degrees Celsius.
  • the frequency characteristic of the amplitude of the exit end of the illumination fiber 12 tends to shift to the low frequency side when the surrounding environment changes from room temperature to high temperature.
  • the frequency characteristic of the resonance frequency fs1 at normal temperature shifts to the low frequency side when the surrounding environment becomes high temperature, and the resonance frequency shifts to the frequency fs2 having a shorter wavelength than the frequency fs1. That is, the amplitude at the same frequency changes before and after the environmental change.
  • the amount of change ⁇ a in amplitude due to environmental changes is smaller in the frequency region far from the resonance frequency fs than in the frequency region near the resonance frequency fs.
  • the amount of change ⁇ as in amplitude at the resonance frequency fs1 at room temperature is a large amount of about 30% of the amplitude at room temperature.
  • the amount of change ⁇ al of the amplitude at the frequency fl in the frequency region away from the resonance frequency fs1 falls within a small value of about several percent of the amplitude at normal temperature.
  • the amplitude of the emission end of the illumination fiber 12 changes, the scanning range of the irradiation light changes, and the angle of view of the image obtained from the light receiving fiber 13 also changes.
  • a target value is set for the angle of view. Therefore, based on the target value, an upper limit value (second threshold value) of the rate of change in allowable amplitude is set in advance, and the emission end of the illumination fiber 12 input from the frequency characteristic calculation unit 101 is set.
  • the frequency fl2 at which the ratio of the amplitude change amount ⁇ al before and after the environmental change becomes equal to the second threshold is obtained.
  • a frequency region having the frequency fl2 as a lower limit is set as a drive frequency region.
  • the frequency fl2 is calculated at which the ratio of the amplitude change amount ⁇ al before and after the environmental change to the amplitude at normal temperature is 5%. To do. Then, a frequency region having the frequency fl2 as a lower limit is set as a drive frequency region.
  • a frequency fl2 ′ is calculated on the lower frequency side than the resonance frequency fs1 so that the ratio of the amplitude change amount ⁇ a before and after the environmental change to the amplitude at normal temperature is 5%. Then, the frequency region having the upper limit of the frequency fl2 ′ is set as the driving frequency region.
  • the frequency characteristic calculation unit 101 can be configured by a general-purpose computer such as a personal computer.
  • the drive frequency region is calculated using the slope of the frequency characteristic of the amplitude of the emission end of the illumination fiber 12 and stored in the memory 16. The operation for recording will be described.
  • the factory worker arranges each part of the optical scanning observation system 1 Connect and turn on the power.
  • the predetermined temperature TEM is a temperature that falls within a normal temperature range such as 25 degrees Celsius.
  • the factory worker gives an instruction to the controller 25 to start scanning by the endoscope 2 by operating a scanning start switch (not shown) of the input device 5, for example.
  • the scanning control unit 25b When the scanning start switch of the input device 5 is operated, the scanning control unit 25b performs control for generating a driving signal having a predetermined driving voltage and a predetermined driving frequency based on the control information read from the memory 24. This is performed for the driver unit 22.
  • the predetermined drive voltage means that the angle of view is within an allowable range even when the actuator unit 15 is driven at the resonance frequency fs, and the amplitude of the emission end of the illumination fiber 12 is determined by the amplitude detector 100.
  • the drive voltage is within a detectable range.
  • the predetermined drive frequency is a drive frequency that continuously changes the frequency in a range from a frequency lower than the resonance frequency fs by a predetermined value to a frequency higher than the resonance frequency fs by a predetermined value. For example, when the resonance frequency is 9000 Hz, control for generating a drive signal that changes the drive frequency of the actuator unit 15 in the range of 8500 Hz to 9500 Hz is input to the driver unit 22.
  • the amplitude detector 100 detects the peristaltic width (amplitude) of the exit end of the illumination fiber 12 in the X-axis direction and the Y-axis direction, and outputs the detected amplitude to the frequency characteristic calculation unit 101.
  • the frequency characteristic calculation unit 101 calculates the frequency characteristic of the amplitude using the amplitude of the emission end of the illumination fiber 12 input from the amplitude detector 100 and the drive frequency of the actuator unit 15.
  • a frequency at which the calculated slope of the frequency characteristic is a first threshold value set in advance is obtained.
  • the obtained frequency is higher than the resonance frequency fs, it is stored in the memory 16 as the lower limit value of the driving frequency of the actuator unit 15 during high frequency driving.
  • the obtained frequency is lower than the resonance frequency fs, it is stored in the memory 16 as the upper limit value of the driving frequency of the actuator unit 15 at the time of low frequency driving.
  • the fact that the calculation and recording of the drive frequency region is completed is output to the scanning control unit 25b.
  • the scanning control unit 25b displays an image of control for causing the display device 4 to display a character string or the like for notifying the factory worker that the calculation and recording of the drive frequency region output from the frequency characteristic calculation unit 101 has been completed. This is performed on the generation unit 25c.
  • the calculation of the drive frequency region of the actuator unit 15 and the recording to the memory 16 are completed using the slope of the frequency characteristic of the amplitude of the emission end of the illumination fiber 12 at a predetermined temperature TEM. .
  • the drive frequency region is calculated using the amplitude shift amount of the emission end of the illumination fiber 12 and recorded in the memory 16. The operation in this case will be described.
  • the factory worker arranges each part of the optical scanning observation system 1 Connect and turn on the power.
  • the predetermined temperature TEM is a temperature that falls within a normal temperature range such as 25 degrees Celsius.
  • the factory worker gives an instruction to the controller 25 to start scanning by the endoscope 2 by operating a scanning start switch (not shown) of the input device 5, for example.
  • the scanning control unit 25b When the scanning start switch of the input device 5 is operated, the scanning control unit 25b performs control for generating a driving signal having a predetermined driving voltage and a predetermined driving frequency based on the control information read from the memory 24. This is performed for the driver unit 22.
  • the predetermined drive voltage means that the angle of view is within an allowable range even when the actuator unit 15 is driven at the resonance frequency fs, and the amplitude of the emission end of the illumination fiber 12 is determined by the amplitude detector 100.
  • the drive voltage is within a detectable range.
  • the predetermined drive frequency is a drive frequency that continuously changes the frequency in a range from a frequency lower than the resonance frequency fs by a predetermined value to a frequency higher than the resonance frequency fs by a predetermined value. For example, when the resonance frequency is 9000 Hz, control for generating a drive signal that changes the drive frequency of the actuator unit 15 in the range of 8500 Hz to 9500 Hz is input to the driver unit 22.
  • the amplitude detector 100 detects the peristaltic width (amplitude) of the exit end of the illumination fiber 12 in the X-axis direction and the Y-axis direction, and outputs the detected amplitude to the frequency characteristic calculation unit 101.
  • the frequency characteristic calculation unit 101 calculates the frequency characteristic of the amplitude at the temperature TEM using the amplitude of the emission end of the illumination fiber 12 input from the amplitude detector 100 and the drive frequency of the actuator unit 15.
  • the factory worker places the endoscope 2 in an environment where the temperature of the actuator unit 15 becomes a predetermined temperature TEB.
  • the predetermined temperature TEB is assumed to be a temperature belonging to a high temperature range such as 37 degrees Celsius.
  • the amplitude detector 100 continuously detects the peristaltic widths (amplitudes) of the exit end of the illumination fiber 12 in the X-axis direction and the Y-axis direction, and outputs the detected amplitude to the frequency characteristic calculation unit 101.
  • the frequency characteristic calculation unit 101 calculates the frequency characteristic of the amplitude at the time of temperature TEB using the amplitude of the emission end of the illumination fiber 12 input from the amplitude detector 100 and the drive frequency of the actuator unit 15.
  • the frequency characteristic calculating unit 101 uses the frequency characteristic of the amplitude at the temperature TEM and the frequency characteristic of the amplitude at the temperature TEB to obtain a frequency at which the ratio of the amplitude change amount ⁇ a is equal to the second threshold value.
  • the obtained frequency is higher than the resonance frequency fs, it is stored in the memory 16 as the lower limit value of the driving frequency of the actuator unit 15 during high frequency driving.
  • the obtained frequency is lower than the resonance frequency fs, it is stored in the memory 16 as the upper limit value of the driving frequency of the actuator unit 15 at the time of low frequency driving. Then, after storing the calculated drive frequency region in the memory 16, the fact that the calculation and recording of the drive frequency region is completed is output to the scanning control unit 25b.
  • the scanning control unit 25b displays an image of control for causing the display device 4 to display a character string or the like for notifying the factory worker that the calculation and recording of the drive frequency region output from the frequency characteristic calculation unit 101 has been completed. This is performed on the generation unit 25c.
  • the calculation of the drive frequency region of the actuator unit 15 and the recording to the memory 16 are completed using the slope of the frequency characteristic of the amplitude of the emission end of the illumination fiber 12 at a predetermined temperature TEM. .
  • the frequency characteristic of the amplitude of the emission end of the illumination fiber 12 is acquired, and the inclination is equal to or less than the first threshold value.
  • the frequency region or the frequency region in which the ratio of the amplitude change amount when the frequency characteristic is shifted is equal to or smaller than the second threshold value is recorded in the memory 16 as the drive frequency region of the actuator unit 15.
  • the actuator unit 15 is driven at a frequency within the drive frequency region recorded in the memory 16, so that the illumination fiber 12 can be emitted even if the use environment of the endoscope 2 changes.
  • the amplitude of the end can be controlled stably.
  • FIG. 8 is a diagram showing another example of the configuration of the main part of the scanning endoscope system according to the embodiment of the present invention.
  • the frequency characteristic calculation unit 101 is arranged separately from the endoscope 2 and the main body device 3.
  • the frequency characteristic calculation unit 101 is arranged in, for example, the controller 25 of the main body device 3. You may comprise as follows.
  • each “unit” in this specification is a conceptual one corresponding to each function of the embodiment, and does not necessarily correspond to a specific hardware or software routine on a one-to-one basis. Therefore, in the present specification, the embodiment has been described assuming a virtual circuit block (unit) having each function of the embodiment.
  • each step of each procedure in the present embodiment may be executed in a different order for each execution by changing the execution order and performing a plurality of steps at the same time, as long as it does not contradict its nature.
  • all or part of each step of each procedure in the present embodiment may be realized by hardware.
  • the frequency region that is not easily affected by the shift of the frequency characteristic accompanying the environmental change is specified, and the same frequency region is set as the driving frequency, so that the fiber can be used regardless of the environmental change.
  • the amplitude can be controlled stably.

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Abstract

L'invention concerne un système d'endoscope de balayage qui a un endoscope 2 qui comprend : une fibre d'éclairage 12 pour guider la lumière d'éclairage pour éclairer un sujet, et délivrer la lumière d'éclairage à partir d'une extrémité de sortie ; et une unité d'actionneur 15 qui oscille l'extrémité de sortie de la fibre d'éclairage 12 selon la tension ou le courant d'un signal électrique appliqué dans le but de balayer la lumière d'éclairage sur le sujet. Le système d'endoscope de balayage comporte également une unité de commande 22 qui applique, à l'unité d'actionneur 15, un signal électrique ayant, en tant que fréquence d'entraînement, une fréquence ayant une quantité de changement d'amplitude égale ou inférieure à une valeur prédéterminée même si les caractéristiques de fréquence de l'amplitude, au moment où l'extrémité de sortie de la fibre d'éclairage 12 oscille, changent en raison d'un changement de conditions d'utilisation de l'endoscope 2.
PCT/JP2015/073153 2015-03-12 2015-08-18 Système d'endoscope de balayage WO2016143160A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
DE112015006046.4T DE112015006046T5 (de) 2015-03-12 2015-08-18 Abtast-Endoskopsystem
CN201580077635.4A CN107405044A (zh) 2015-03-12 2015-08-18 扫描型内窥镜系统
JP2016520120A JP6143953B2 (ja) 2015-03-12 2015-08-18 走査型内視鏡システム
US15/698,906 US20180014719A1 (en) 2015-03-12 2017-09-08 Scanning endoscope system

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JP2015-049801 2015-03-12
JP2015049801 2015-03-12

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US15/698,906 Continuation US20180014719A1 (en) 2015-03-12 2017-09-08 Scanning endoscope system

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KR102301809B1 (ko) * 2019-05-02 2021-09-15 (주) 브이픽스메디칼 리사주 기반의 이미지 캘리브레이션 기술

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DE112015006046T5 (de) 2017-11-23
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CN107405044A (zh) 2017-11-28
JP6143953B2 (ja) 2017-06-07

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